CN108289635B

CN108289635B - Magnetic resonance imaging system and related method

Info

Publication number: CN108289635B
Application number: CN201680066841.XA
Authority: CN
Inventors: S-K.李; E.菲夫兰; J.皮尔; B.科利克
Original assignee: General Electric Co
Current assignee: General Electric Co
Priority date: 2015-11-12
Filing date: 2016-11-09
Publication date: 2021-12-28
Anticipated expiration: 2036-11-09
Also published as: KR20180071366A; WO2017083376A1; US10527694B2; KR102587374B1; CN108289635A; US20170139022A1

Abstract

A magnetic resonance imaging system is disclosed. A magnetic resonance imaging system includes a magnetic core that generates a magnetic field including a plurality of magnetic field lines. The magnetic resonance imaging system also includes a plurality of gradient coils disposed along the magnetic core, and a plurality of gradient amplifiers. In addition, the magnetic resonance imaging system includes a plurality of bus conductors connecting corresponding ones of the plurality of gradient coils and corresponding ones of the plurality of gradient amplifiers. The plurality of busbar conductors are disposed along at least one of a first path extending along the plurality of magnetic field lines and a second path extending in a substantially linear direction from the corresponding gradient coil to a fringe region of the magnetic field to reduce an effect of the lorentz force on the plurality of busbar conductors.

Description

Magnetic resonance imaging system and related method

Cross Reference to Related Applications

This application claims priority to U.S. patent application No. 14/938,891 filed 11/12/2015, which is incorporated herein by reference in its entirety.

Technical Field

Embodiments of the present invention relate generally to magnetic resonance imaging systems and, more particularly, to busbar conductors for use in magnetic resonance imaging systems.

Background

In Magnetic Resonance Imaging (MRI) systems, electrical bus-bar conductors (electrical bus-bar conductors) transmit electrical current from a gradient driver (gradient driver) to a gradient coil (gradient coil). In plug-in gradient coil MRI systems, the gradient coils are often much shorter than the magnetic core. Therefore, the busbar conductors need to be extended significantly closer to the iso-center of the magnet in order to connect to the gradient coils. In particular, a significant length of busbar conductor is disposed in the region affected by the strong magnetic field generated by the magnetic core. The portion of the busbar conductors adjacent to the magnetic core is subjected to a strong lorentz force due to the magnetic field.

The busbar conductor is subjected to severe vibration due to lorentz force. Vibrations of the busbar conductors may also cause mechanical shaking of the patient table and generate acoustic noise in the MRI system.

The lorentz force also causes intermittent contact between the filaments corresponding to the busbar conductors and the joints. The metal-metal contact between the filament and the joint causes the generation of an electrical discharge. As a result, white pixel artifacts are generated. Thus, the quality of the acquired image is deteriorated.

Therefore, there is a need for a compact and simple design of the busbar conductors to minimize the effects of lorentz forces in the MRI system.

Disclosure of Invention

According to one embodiment of the invention, a magnetic resonance imaging system is disclosed. A magnetic resonance imaging system includes a magnetic core that generates a magnetic field that includes a plurality of magnetic field lines. The magnetic resonance imaging system also includes a plurality of gradient coils disposed along the magnetic core, and a plurality of gradient amplifiers. In addition, the magnetic resonance imaging system includes a plurality of bus bar conductors connecting corresponding ones of the plurality of gradient coils and corresponding ones of the plurality of gradient amplifiers. The plurality of buss line conductors are disposed along at least one of a first path extending along the plurality of magnetic field lines and a second path extending in a substantially linear direction from the corresponding gradient coil to a fringe region of the magnetic field.

According to another embodiment of the invention, a method for installing a magnetic resonance imaging system is disclosed. The method includes connecting a plurality of busbar conductors to corresponding ones of the plurality of gradient coils and corresponding ones of the plurality of gradient amplifiers. A plurality of gradient coils are disposed along a magnetic core configured to generate a magnetic field comprising a plurality of magnetic field lines. Further, the method includes disposing a plurality of busbar conductors along at least one of a first path extending along the plurality of magnetic field lines and a second path extending along a substantially linear direction from the corresponding gradient coil to a fringe region of the magnetic field.

According to yet another embodiment of the invention, a method for operating a magnetic resonance imaging system is disclosed. The method includes generating a magnetic field including a plurality of magnetic field lines using a magnetic core. The magnetic resonance imaging system includes a plurality of gradient coils disposed along the magnetic core, a plurality of gradient amplifiers, and a plurality of bus bar conductors connecting corresponding ones of the plurality of gradient coils and corresponding ones of the plurality of gradient amplifiers. The plurality of buss line conductors are disposed along at least one of a first path extending along the plurality of magnetic field lines and a second path extending in a substantially linear direction from the corresponding gradient coil to a fringe region of the magnetic field. Additionally, the method includes transmitting current through the plurality of busbar conductors such that the effect of lorentz force on the plurality of busbar conductors is minimized.

Drawings

These and other features, aspects, and advantages of the present invention will become better understood when the following detailed description is read with reference to the accompanying drawings in which like characters represent like parts throughout the drawings, wherein:

figure 1 is a diagrammatic view of a magnetic resonance imaging system;

figure 2 is a diagrammatic view of a magnetic resonance imaging system according to an exemplary embodiment of the present invention;

figure 3 is a diagrammatic view of a magnetic resonance imaging system according to the embodiment of figure 2;

figure 4 is a diagrammatic view of a magnetic resonance imaging system according to another exemplary embodiment of the present invention;

fig. 5 is an illustrative embodiment of a busbar conductor according to the embodiment of fig. 4;

figure 6 is a diagrammatic view of a magnetic resonance imaging system according to yet another embodiment;

figure 7 is a diagrammatic view of a magnetic resonance imaging system according to yet another exemplary embodiment;

fig. 8 is an illustrative embodiment of a busbar conductor according to the embodiment of fig. 7; and is

Figure 9 is an illustrative embodiment of a magnetic resonance imaging system in accordance with yet another exemplary embodiment.

Detailed Description

Unless defined otherwise, technical and scientific terms used herein have the same meaning as commonly understood by one of ordinary skill in the art to which this specification belongs. As used herein, the terms "first," "second," and the like, do not denote any order, quantity, or importance, but rather are used to distinguish one element from another. Furthermore, the terms a, an, and the like do not denote a limitation of quantity, but rather denote the presence of at least one of the referenced item. The term "or" is intended to be inclusive and mean one, some, or all of the listed items. The use of "including" or "comprising" and variations thereof herein is meant to encompass the items listed thereafter and equivalents thereof as well as additional items. The terms "connected" and "connected" are not limited to physical or mechanical connections or connections, and may include electrical connections or connections, whether direct or indirect. Further, terms such as "circuit" (a circuit) "," circuit "(a controller)" and "controller" may include a single component or multiple components that are active and/or passive and are connected or otherwise coupled together to provide the described functionality. Also, the term operatively connected as used herein includes wired connection, wireless connection, electrical connection, magnetic connection, wireless communication, software-based communication, or a combination thereof.

As will be described in detail below, various embodiments of an exemplary magnetic resonance imaging system and methods of installing and operating a magnetic resonance imaging system are disclosed. In particular, a busbar arrangement in an interposed gradient coil magnetic resonance imaging system is disclosed.

Turning now to the drawings, and referring to FIG. 1, a conventional magnetic resonance imaging system 100 is illustrated. The conventional MRI system 100 includes an MRI scanner 101 having a magnetic core 102 and a plurality of gradient coils 104. The core 102 is configured to generate a magnetic field having a plurality of magnetic field lines.

The MRI system 100 further includes a plurality of gradient amplifiers 108. Each of the gradient coils 104 is operatively connected to a corresponding gradient amplifier 108 via a plurality of bus bar conductors 106. Reference numeral 114 denotes a filter configured to filter any noise in the current transmitted from the gradient amplifier 108 to the gradient coil 104. The plurality of busbar conductors 106 are held together using a support structure 110. The gradient coil ends 112 of the busbar conductors 106 are rigidly secured to the flanges of the magnetic core.

In the MRI system 100, the gradient coil 104 may be much shorter in length than the magnetic core 102. In this case, the busbar conductors 106 need to extend substantially into the magnetic core 102 in order to be connected to the gradient coil 104. Thus, the busbar conductor 106 is disposed in a region affected by a strong magnetic field. Further, the bus bar conductors 106 are arranged in such a manner that the direction of current transmission through the bus bar conductors 106 is not parallel to the magnetic field lines. In addition, for a length of busbar conductor 106, the busbar conductor 106 is disposed in an area that is affected by a strong magnetic field. Accordingly, the lorentz force acting on the busbar conductors 106 is considerably high. Accordingly, the MRI system 100 is subjected to excessive vibration.

Referring now to fig. 2, fig. 2 depicts a diagrammatic view of a magnetic resonance imaging system 200 in accordance with an embodiment of the present invention. A Magnetic Resonance Imaging (MRI) system 200 includes an MRI scanner 202 configured to receive and scan a patient.

The MRI scanner 202 includes a magnetic core 204 and a plurality of gradient coils 206. The core 204 is configured to generate a magnetic field having a plurality of magnetic field lines. The magnetic field includes a radial magnetic field component and an axial magnetic field component. The term "magnetic field" as used herein may be used to refer to the absolute value of the vector sum of the radial and axial magnetic field components. A plurality of gradient coils 206 are disposed along the magnetic core 204. The gradient coil 206 is a high performance plug-in gradient coil. The gradient coil 206 has a shorter length than the magnetic core 204. In one embodiment, the gradient coil 206 is about 30 centimeters to about 80 centimeters shorter than the magnetic core 204.

Gradient coil 206 includes an X-axis coil 220, a Y-axis coil 222, and a Z-axis coil 224. In addition, the MRI system 200 includes a plurality of gradient amplifiers 210. In one embodiment, the gradient amplifier 210 includes an X-axis amplifier 214, a Y-axis amplifier 216, and a Z-axis amplifier 218.

In the illustrated embodiment, the MRI scanner 202 is positioned at a first location 201 and the gradient amplifier 210 is disposed at a second location 203. The first location 201 is a scanning chamber and the second location 203 is an equipment chamber. The first location 201 and the second location 203 are separated from each other by a penetrating wall 205. Furthermore, a filter 212 is positioned on the penetrating wall 205. The filter 212 is configured to filter any noise in the current transmitted from the gradient amplifier 210 to the gradient coil 206. The term "noise" as used herein may be used to refer to any non-uniformity of the current.

Specifically, an X-axis coil 220, a Y-axis coil 222, and a Z-axis coil 224 are connected to the X-axis amplifier 214, the Y-axis amplifier 216, and the Z-axis amplifier 218, respectively. In one non-limiting example, a gradient amplifier 210 corresponding to each gradient coil 206 controls the current transmitted to the gradient coil 206. Current is transmitted from the gradient amplifier 210 to the corresponding gradient coil 206 via a plurality of bus bar conductors 208. Specifically, each of the gradient coils 206 is connected to a corresponding gradient amplifier 210 via at least two busline conductors 208. One of the busbar conductors 208 is connected to the positive terminal and the other of the busbar conductors 208 is connected to the negative terminal. In one embodiment, each of the bus bar conductors 208 is made of copper. The electrical current delivered to the gradient coils 206 helps to generate a magnetic field having a desired gradient in the MRI scanner 202.

According to an embodiment of the present invention, the plurality of busbar conductors 208 are disposed along the first path such that the direction of current passing through the busbar conductors 208 is parallel to the magnetic field lines. In another embodiment, the plurality of busbar conductors 208 are disposed along the second path such that the second path extends in a substantially linear direction from the corresponding gradient coil 206 to an edge region of the magnetic field. Thus, the busbar conductors 208 experience a minimum lorentz force. Due to the minimization of the lorentz force, vibrations in the MRI system 200 are greatly reduced. Details regarding the first path and the second path are discussed in more detail with reference to subsequent figures.

Figure 3 is a diagrammatic view of the magnetic resonance imaging system 200 of figure 2 in accordance with an embodiment of the present invention. The MRI system 200 includes a magnetic core 204 and a plurality of gradient coils 206. Each of the gradient coils 206 includes a positive terminal 304 and a negative terminal 306. The core 204 is configured to generate a magnetic field 307 having a plurality of magnetic field lines 308.

Reference numeral 310 denotes a vertical axis r (m) indicating a radial distance in meters from the center of the core 204 to the position where the magnetic field is calculated. Specifically, the magnetic field lines 308 extend within a radial distance range of about 0.2 meters to about 1.05 meters from the center of the core 204. Reference numeral 312 denotes a horizontal axis z (m) indicating the axial distance in meters from the center of the core 204 to the position where the magnetic field is calculated.

Reference numerals

314 and 316 denote first paths. Specifically, reference numeral 314 denotes a first path from the positive terminal 304 to the magnetic core 204. Further, reference numeral 316 denotes a first path from the negative terminal 306 to the core 204. The

first paths

314, 316 are determined based on the position of the core 204 and the corresponding pattern of magnetic field lines 308.

The shape of the

first paths

314, 316 is such that if any current carrying busbar conductors are positioned along the

first paths

314, 316, the direction of current transmission through the busbar conductors is parallel to the magnetic field lines 308. In the illustrated embodiment, the current transmission direction is represented by

reference numerals

318, 320. Specifically, reference numeral 318 denotes a current transmission direction along the first path 316 and reference numeral 320 denotes a current transmission direction along the first path 314. In particular, the direction of current flow along the

first path

314, 316 at any point on the busbar conductor is parallel to the magnetic field lines 308. The arrangement of the busbar conductors along the first path helps to minimise the effect of lorentz forces on the busbar conductors.

Referring now to fig. 4, a diagram of a magnetic resonance imaging system 400 according to another exemplary embodiment is depicted. Gradient coil 206 includes an X-axis coil 220, a Y-axis coil 222, and a Z-axis coil 224. Each of the X-axis coil 220, the Y-axis coil 222, and the Z-axis coil 224 includes a positive terminal and a negative terminal. The gradient amplifier 210 includes an X-axis amplifier 214, a Y-axis amplifier 216, and a Z-axis amplifier 218. The X-axis coil 220, Y-axis coil 222, and Z-axis coil 224 are connected to the X-axis amplifier 214, Y-axis amplifier 216, and Z-axis amplifier 218, respectively. The gradient coils 206 are operatively connected to the gradient amplifier 210 via a plurality of bussing line conductors 402. Each of the X-axis coil 220, the Y-axis coil 222, and the Z-axis coil 224 is connected to a corresponding gradient amplifier 210 via two bus conductors 402. Thus, the gradient coils 206 are connected to corresponding gradient amplifiers 210 via six busline conductors 402. Furthermore, the MRI system 400 includes a filter 212, the filter 212 configured to filter any noise in the current transmitted from the gradient amplifier 210 to the gradient coil 206.

In the illustrated embodiment, the busbar conductor 402 has two

portions

404 and 406. The portion 404 of the busbar conductor 402 is disposed in a region that is affected by the magnetic field generated by the magnetic core 204. The portion 406 of the busbar conductor 402 is disposed in a region that is subject to negligible influence from the magnetic field generated by the magnetic core 204. A portion 404 of the busbar conductor 402 extends from the positive and negative terminals of the gradient coil 206 to a service end flange 408 of the magnetic core 204. Further, a portion 406 of the busbar conductor 402 extends from one end of the portion 404 of the busbar conductor 402 (adjacent to the service end flange 408) to the gradient amplifier 210. Specifically, a portion 404 of the bus bar conductor 402 is connected to the positive and negative terminals of the gradient coil 206, and a portion 406 of the bus bar conductor 402 is connected to the gradient amplifier 210.

The portion 404 of the busbar conductor 402 is arranged along a first path (similar to the

first paths

314, 316 of figure 3) such that the effect of the lorentz force on the busbar conductor 402 is reduced. In one embodiment, the Lorentz force acting on the portion 404 disposed along the first path is almost zero. In the illustrated embodiment, the portion 404 of the busbar conductor 402 has a curved shape. In other embodiments, the shape of the busbar conductors 402 may vary depending on the magnetic field lines.

Fig. 5 is an illustrative embodiment of a busbar conductor 402 according to the embodiment of fig. 4. Specifically, a portion 404 of the busbar conductor 402 is depicted. In the illustrated embodiment, two bus bar conductors 402 are depicted. In other embodiments, the number of busbar conductors 402 may vary depending on the application.

In one embodiment, the busbar conductor 402 is a flexible conductor. In such an embodiment, the busbar conductor 402 is cut to a predetermined length from a heavy-duty cable made of copper. Furthermore, a support structure 506 is connected to the portion 404 of the busbar conductor 402 so as to support the portion 404 of the busbar conductor 402. The portion 404 of the busbar conductor 402 is connected to the support structure 506 via a fastening unit 508. In one embodiment, the support structure 506 is made of an insulating material. The insulating material may comprise glass, plastic, polymer, wood, or a combination thereof. The insulating material is configured to take the shape of an area and is positioned between the busbar conductors 402 as depicted.

In the illustrated embodiment, in particular, the support structure 506 includes a plurality of grooves 512. The portions 404 of the busbar conductors 402 are disposed in corresponding grooves 512 and secured to the grooves 512 using securing units 508. In one example, the fastening unit 508 may include an adhesive tape. The first ends 514 of the portions 404 of the busbar conductors 402 are connected to positive and negative terminals of the gradient coils, such as the positive and

negative terminals

304, 306 of fig. 3, using bolts 510. The other end 516 of the portion 404 of the busbar conductor 402 is connected to a portion 406 of the busbar conductor, which portion 406 is connected to a gradient amplifier such as the gradient amplifier 210 of figure 2. In another embodiment, the busbar conductor 402 is a rigid conductor. In such an embodiment, the busbar conductor 402 is made by rolling or cutting a copper strip.

Figure 6 is a diagrammatic representation of another embodiment of a magnetic resonance imaging system 600. The MRI system 600 includes a magnetic core 204 and a gradient coil 206. The gradient coil 206 includes a positive terminal 304 and a negative terminal 306. Magnetic core 204 is configured to generate a magnetic field, such as magnetic field 307 of fig. 3. In the illustrated embodiment, the radial component of the magnetic field is represented. In the illustrated embodiment, the region affected by the magnetic field has a first region 602, a second region 604, and a third region 606. The first region 602 is affected by a strong radial magnetic field. The second region 604 is affected by a radial magnetic field of reduced strength compared to the radial magnetic field of the first region 602. The third region 606 is referred to as an edge region of the magnetic field. The terms "third region" and "edge region of the magnetic field" are used interchangeably. The radial magnetic field strength corresponding to the third region 606 is less than the radial magnetic field strength corresponding to the first region 602 and the second region 604.

Reference numeral 603 denotes a vertical axis r (m) indicating the radial distance in meters from the center of the core 204 to the position where the magnetic field is calculated. Reference numeral 605 denotes a horizontal axis z (m) indicating the axial distance in meters from the center of the core 204 to the position where the magnetic field is calculated. Further, reference numeral 612 denotes a scale indicating the unit of radial magnetic field in tesla.

As noted above, the plurality of busbar conductors are configured to operably connect the gradient coils 206 to corresponding gradient amplifiers. In the embodiment of fig. 6, the busbar conductors are disposed along

second paths

608, 610. A second path 608 extends from the positive terminal 304 and a second path 610 extends from the negative terminal 306. In particular, each of the

second paths

608, 610 extends in a substantially linear direction from the corresponding gradient coil 206 to the edge region 606 of the magnetic field 307. Each of the

second paths

608, 610 indicates the shortest distance path from the gradient coil 206 to the edge region 606 of the magnetic field 307. In one embodiment, each of the

second paths

608, 610 extends substantially linearly along the axial direction of the magnetic core 204. In the illustrated embodiment, because the

second paths

608, 610 indicate the shortest distance from the gradient coil 206 to the edge region 606 of the magnetic field 307, the lorentz forces acting on the busbar conductors disposed along the

second paths

608, 610 are minimized. In one embodiment, the lorentz force acting on the busbar conductors may be reduced by about 30% to about 90% when compared to the lorentz force in a conventional plug-in gradient coil MRI system.

Referring to fig. 7, a magnetic resonance imaging system 700 according to another embodiment of the invention is depicted. Specifically, fig. 7 shows the busbar conductors 702 disposed along a second path, such as the

second paths

608, 610 of fig. 6. The MRI system 700 includes an MRI scanner 202 having a magnetic core 204 and a plurality of gradient coils 206. The gradient coils 206 are operatively connected to the gradient amplifier 210 via a plurality of bussing conductors 702. The bus bar conductor 702 has a flat shape. Furthermore, the MRI system 700 includes a filter 212, the filter 212 configured to filter any noise in the current transmitted from the gradient amplifier 210 to the gradient coil 206.

The busbar conductor 702 has two

sections

704, 706 along the length of the busbar conductor 702. A portion 704 of the busbar conductor 702 is disposed in a region that is affected by the magnetic field generated by the magnetic core 204. The portion 706 of the busbar conductor 702 is disposed in a region that is subject to negligible influence from the magnetic field generated by the magnetic core 204. The portion 704 of the busbar conductor 702 extends from the positive and negative terminals of the gradient coil 206 to the fringe region of the magnetic field via a shortest distance path. In particular, the portion 704 of the busbar conductor 702 represents a second path that extends in a substantially linear direction from the corresponding gradient coil 206 to the fringe region of the magnetic field.

Fig. 8 is an illustrative embodiment of a busbar conductor 702 according to the embodiment of fig. 7. In one non-limiting example, the busbar conductor 702 may be made of 3/0AWG copper cable. In the illustrated embodiment, a set of busbar conductors 702 is depicted. Specifically, a portion 704 (shown in fig. 7) of a set of busbar conductors 702 is depicted. A portion 704 of the busbar conductor 702 is held between two panels 802 bolted together by a fastening unit, such as a plurality of brass bolts 804. Further, the strap 806 is fastened to the two panels 802 using a fastening unit, such as an adhesive tape 808. The band 806 and the faceplate 802 may be made of an insulating material such as, but not limited to, a transparent plastic such as a polymethylmethacrylate material, or an acrylic or acrylic glass or acrylic plastic (e.g., plexiglas)^TM)。

The two terminals 810 of the busbar conductor 702 are connected to a crimp terminal sleeve (crimp lug). The term "crimp terminal sleeve" as used herein refers to a metallic end piece. In one embodiment, two terminals 810 are separated by a distance of 5.0 cm. The two terminals 810 are further connected to the positive and negative terminals of the gradient coil. In another embodiment, the length of the portion 704 of the busbar conductor 702 is 3 feet. In yet another embodiment, the lateral gap (from center to center) between the two busbar conductors 702 is about 35 mm.

Figure 9 is an illustrative embodiment of a magnetic resonance imaging system 700 according to the exemplary embodiment of figure 8. The MRI system 700 further includes a rigid aluminum frame 902 for holding the busbar conductors 702. Specifically, the rigid aluminum frame 902 is connected to the busbar conductor 702 using a solid plastic block 904 and bolts 906. In the illustrated embodiment, the rigid aluminum frame 902 is a rectangular structure. The rigid aluminum frame 902 is also connected to the service-end flange 408 of the core via a fastening unit.

According to embodiments discussed herein, the busbar conductors in a magnetic resonance imaging system are arranged in a manner such that lorentz forces on the busbar conductors are minimized. Vibration of the busbar conductors and other components of the MRI system is minimized due to the reduction of the lorentz force. Thus, mechanical rocking of any hardware associated with the MRI scanner is reduced. Furthermore, acoustic noise in the exemplary MRI system is minimized. This arrangement of the busbar conductors reduces intermittent metal-to-metal contact, thereby reducing the generation of electrical discharges. Thus, white pixel artifacts are significantly reduced. Therefore, good quality images are obtained using the MRI system.

While the invention has been described with reference to exemplary embodiments, it will be understood by those skilled in the art that various changes may be made and equivalents may be substituted for elements thereof without departing from the scope of the invention. In addition, many modifications may be made to adapt a particular situation or material to the teachings of the invention without departing from the essential scope thereof. Therefore, it is intended that the invention not be limited to the particular embodiment disclosed as the best mode contemplated for carrying out this invention, but that the invention will include all embodiments falling within the scope of the appended claims.

Claims

1. A magnetic resonance imaging system comprising:

a magnetic core generating a magnetic field comprising a plurality of magnetic field lines;

a plurality of gradient coils disposed along the magnetic core;

a plurality of gradient amplifiers; and

a plurality of busbar conductors connecting corresponding gradient coils of the plurality of gradient coils and corresponding gradient amplifiers of the plurality of gradient amplifiers, wherein the plurality of busbar conductors are disposed along at least one of a first path extending along the plurality of magnetic field lines in a radial-axial plane and a second path extending along a substantially linear direction from the corresponding gradient coils to a fringe region of the magnetic field.

2. The magnetic resonance imaging system of claim 1, characterized in that: further comprising a support structure connected to the plurality of busbar conductors for supporting the plurality of busbar conductors.

3. The magnetic resonance imaging system of claim 2, characterized in that: further comprising a fastening unit for fastening the plurality of busbar conductors to the support structure.

4. The magnetic resonance imaging system of claim 2, characterized in that: at least one of the plurality of busbar conductors comprises a copper strip.

5. The magnetic resonance imaging system of claim 2, characterized in that: the support structure includes an insulating material.

6. The magnetic resonance imaging system of claim 5, characterized in that: the insulating material comprises glass, plastic, polymer, wood, or a combination thereof.

7. The magnetic resonance imaging system of claim 1, characterized in that: the first path extends substantially parallel to the plurality of magnetic field lines.

8. The magnetic resonance imaging system of claim 1, characterized in that: at least one of the plurality of bus bar conductors has a curved shape.

9. The magnetic resonance imaging system of claim 1, characterized in that: at least one of the plurality of bus bar conductors has a flat shape.

10. The magnetic resonance imaging system of claim 1, characterized in that: the second path extends substantially linearly in an axial direction of the magnetic core.

11. The magnetic resonance imaging system of claim 1, characterized in that: the plurality of busbar conductors disposed along at least one of the first path and the second path are configured to minimize the effect of lorentz force.

12. A method for installing a magnetic resonance imaging system, the method comprising:

connecting a plurality of bus-bar conductors to corresponding gradient coils of a plurality of gradient coils and corresponding gradient amplifiers of a plurality of gradient amplifiers, wherein the plurality of gradient coils are disposed along a magnetic core configured to generate a magnetic field comprising a plurality of magnetic field lines; and

the plurality of bus bar conductors are disposed along at least one of a first path extending along the plurality of magnetic field lines in a radial-axial plane and a second path extending along a substantially linear direction from the corresponding gradient coil to a fringe region of the magnetic field.

13. The method of claim 12, wherein: further comprising connecting a support structure to the plurality of busbar conductors.

14. The method of claim 13, wherein: further comprising connecting the plurality of busbar conductors to the support structure via a fastening unit.

15. The method of claim 12, wherein: disposing the plurality of busbar conductors along the first path comprises disposing the plurality of busbar conductors substantially parallel to the plurality of magnetic field lines.

16. The method of claim 12, wherein: disposing the plurality of busbar conductors along the second path includes disposing the plurality of busbar conductors substantially linearly along an axial direction of the magnetic core.

17. A method for operating a magnetic resonance imaging system, the method comprising:

generating a magnetic field comprising a plurality of magnetic field lines using a magnetic core, wherein the magnetic resonance imaging system comprises:

a plurality of gradient coils disposed along the magnetic core;

a plurality of gradient amplifiers; and

a plurality of busbar conductors connecting corresponding gradient coils of the plurality of gradient coils and corresponding gradient amplifiers of the plurality of gradient amplifiers, wherein the plurality of busbar conductors are disposed along at least one of a first path extending along the plurality of magnetic field lines in a radial-axial plane and a second path extending along a substantially linear direction from the corresponding gradient coils to a fringe region of the magnetic field; and are

And is

Transmitting a current through the plurality of busbar conductors such that an effect of a lorentz force on the plurality of busbar conductors is minimized.

18. The method of claim 17, wherein: transmitting current through the plurality of busbar conductors includes transmitting current through the plurality of busbar conductors disposed along the first path parallel to a magnetic field line of the plurality of magnetic field lines.